Breath-condensate device

ABSTRACT

A cartridge device (10) for collecting and analysing a breath condensate is disclosed. The device (10) comprises a condensation zone (12) to condense exhaled breath from a subject and cooling means operably connected to the condensation zone (12). The device includes further discrete regions (13) for detection of analyte and measurement of analyte. The condensation zone (12) has a fluid exit connecting the condensation zone (12) to the discrete regions (13).

FIELD OF THE INVENTION

The present invention relates to a device for use in analysing exhaledmammalian breath, especially that of a human, but also of animals suchas horses, dogs, etc. The device is particularly for use in analysingalveolar air, and to be retained, in use, within a housing to aidcollection of breath-condensate.

BACKGROUND OF THE INVENTION

In a previous application, EP2173250, assigned to the Applicant, adevice is described which allows efficient collection of exhaled breath,and in particular collection with a minimal loss of volatile components,which would introduce error into subsequent analyses. Once the breathsample is condensed, it is then made available for analysis. However,analysis needs to be done separately from the device, which means thesample constituents can change in the meantime, affecting the resultsobtained.

Prior art document DE199 51 204 describes a method of condensing exhaledbreath until a predetermined volume of sample is obtained. The samplethus obtained is moved from the storage zone to a detection zone.However, the methodology includes a delay between the collection anddetection so that any inherent instabilities in the sample will affectthe final concentrations determined. For example, the sample hassufficient time to dry out, short-lived species may decompose and thereis a risk of contamination from outside sources.

DE 101 375 65 addresses the problems partially through the provision ofa closed cassette for measurement of breath condensate. Within thedevice, buffer solutions and/or sensor calibration solutions areincluded. However, some of the liquid reagents used have a limited shelflife. Moreover, the operator is required to perform several manualsteps, often using said liquid reagents, which can lead to delay andpotential errors.

SUMMARY OF THE INVENTION

In a first, broad, independent aspect, there is provided a cartridgedevice for collecting and analysing a breath condensate, the devicecomprising a condensation zone, to condense exhaled breath from asubject, the condensation zone being operably connectable to a coolingmeans, the device including one or more further discrete regions fordetection of analyte and measurement of analyte, the cartridge devicefurther comprising a fluid path connecting the condensation zone to theor each discrete region.

This configuration is particularly advantageous because the integratednature of the device allows for minimal interventions from an operatorand therefore increases the accuracy and the reliability of the analysisproduced and condensate from only a single exhaled breath or a shortbreath cycle, taken for example over 60 seconds, is required. Thisconfiguration also minimises the risk of any cross-contamination or lossof sample occurring. The spatial separation of a region from anotherregion allows for regions to be held at different temperatures andconditions, and as the condensate is provided with a natural flow pathinto channels and sensing zones of the discrete regions there is no needfor interference from an operator, thereby removing one of the biggestsources of inaccuracy: user error when performing manual tasks.

The integrated nature of the device also allows for the device to beprovided as a self-contained and removably insertable cartridge partwhich can work in conjunction with a housing to provide a more complexanalysing device. Thus, such a device as described may be provided as areplaceable cartridge for an analysing device.

Preferably, the condensation zone has a lid which at least partiallycovers said condensation zone. This configuration is particularlyadvantageous because a partial lid aids the retention of the condensatewithin the device and channels the breath condensate towards thechannels and the sensing zones.

Preferably, the device includes analysis initiation means to detect thepresence of a condensate.

This configuration is particularly advantageous because it enables thefunctions for analysis of a breath condensate to be carried out in asingle integrated device which decreases any delay and likelihood oferror associated with movement of condensate samples. It provides afurther level of control of the system to produce analysis without needfor an operator involvement.

Preferably, the or each discrete region has a specified volume, whichallows the measurements to be calculated based upon the volumes.

The specified volume may be up to approximately 4 μl.

Preferably, one or more discrete regions has a specified volume suchthat there is an analyte detection zone whose volume is less than thevolume of condensate from one exhaled breath. This allows for themeasurement of a determined volume of the breath condensate.

Preferably, a surface of a discrete region includes a surface coating,said coating including reagents to engage the condensate and determinecomposition.

This configuration is particularly advantageous because it means thereis no necessity for a liquid reagent to be added to the sample thusminimising dilution errors and providing a device which has both anextended shelf life and is easier to manufacture.

Preferably, the surface coating has a thickness in a range of from 1 μmto 15 μm.

Preferably, a discrete region includes 2 or more electrodes in operableconnection with a condensation zone, the electrodes being maintained atdifferent potentials. Further preferably, the potential between the pairof electrodes is variable. The use of electrodes allows accuratedetermination of the analyte and moreover provides a long-lasting meansof analysis, allowing a device to be stored for extended periods withoutdegradation of accuracy.

Optionally, a reagent is added to said condensate in a further discretepreparation region.

This allows the use of chemicals and reagents that would beintrinsically incompatible if formulated together, or stored in intimatecontact to be prepared within the device, except with adequate physicalseparation to prevent interaction, reaction and or degradation duringmanufacturing and storage.

Preferably, one or more regions are temperature controlled.

This configuration is particularly advantageous because the differentfunctions of the device require different temperatures at which to workbest, therefore zones can be held at the same temperature or differenttemperatures and the temperatures can be changed during the operation ofthe device and the temperature within a zone can be controlled relativeto ambient temperature.

Preferably, the reagents for the analysis of the condensate are loadedinto the condensate sample during passage of the condensate sample fromthe condensation zone to a detection zone. This assists in the detectionand analysis of analytes within the condensate.

Preferably, a discrete region has a perimeter ranging from 2-10 mm, andespecially a perimeter of 5 mm.

Preferably a discrete region has a height of approximately from 75-750μm, and especially a height of 100 μm.

A discrete region may comprise a chamber, the chamber being enclosed onfive sides with a sixth side open for fluid to enter the said chamberand for displaced air to escape therefrom.

It is preferred that the condensate forms a film rather than droplets.The described features of the region aid the formation of a film. Filmshave a controlled flow and eliminate the occurrence of air trappedwithin the chamber. Optionally, this is achieved through the selectionof a surface material for the condensation zone having an appropriatecontact angle with the breath condensate. A contact angle of around 20°,is preferred.

Preferably, multiple breath condensates may be collected and analysedsimultaneously, to provide a more efficient device.

Optionally, the device includes transmission means such as a cable,Bluetooth®, Wi-Fi connection to enable information on the analysis to betransmitted to processing and display, allowing a user to review theresults. Interventions from the operator are further minimised thereforeremoving one of the biggest sources of inaccuracy due to user error whenperforming manual tasks.

Preferably, any interference to the determined values are measured andaccounted for in the final signal.

This configuration is particularly advantageous because it allows thesignal to be calibrated to produce an accurate result and with a reducednumber of errors.

Conveniently, the power to the condensation zone is determined enablingcalculation of the flow rate of exhaled breath, or rate of exhaledbreath condensation and the total volume of exhaled breath collected.This has a number of advantages as the efficiency of the device can bedetermined to ensure it remains within acceptable parameters. Also, thevolume can be used to determine the breathing efficiency of the user.

Preferably, the device further comprises a hole or channel through whichair can escape from the device, said hole or channel connecting adiscrete region with atmosphere, so allowing air to leave the device andpreventing air from getting trapped within the device as the breathcondensate flows in.

When the device is part of a more complex device, certain features, asset out elsewhere herein, may be provided as part of a housing of thatcomplex device. For example, means for guiding breath to thecondensation zone may be external to the device in cartridge form, i.e.within the housing, the condensation zone being part of the saidcartridge. The housing may comprise a port for insertion and removal ofa cartridge.

The cartridge device may preferably comprise a cartridge air-shield toshield the cartridge device from direct contact with ambient air, toavoid so far as possible, the co-condensation of ambient humidity thatwould otherwise confound the analysis through dilution of the sample.

The cartridge device may preferably comprise a cartridge light-shield toshield the cartridge device from ambient light, to avoid so far aspossible breakdown of any photoactive species which may be present in abreath sample.

The cartridge device may further comprise a temperature sensor formeasuring breath temperature.

Thus, the cartridge device optionally measures physical and chemicalparameters on the patient's breath including: rate of breath exhalation,the water content of the breath exhalation, the temperature of theexhaled breath, carbon dioxide levels on the exhaled breath, breathpressure etc.

The device is able to monitor these various sensors and use them aboutto give feedback to the user in real-time, so that the user can modulatetheir breathing profile. This feedback can be given in several formsincluding visual or audio.

The cartridge device may be adapted so that when the cartridge devicehas determined that sufficient condensate has been collected it is ableto electrically activate the cartridge and make measurements upon theexhaled breath condensate, thus determining the concentration ofanalytes within the exhaled breath condensate.

Optionally, the assay is automatically started when a cartridge-filledcondition is met, such as the electrical shorting of two electrodes bythe liquid sample.

The analytes are optionally converted by an enzymatic reaction into anelectrochemically active molecule, which is detected by electrochemicalanalysis. The enzyme formulation is either a soluble or an insolubleformulation. The soluble formulation enables the enzyme or enzymes todissolve into the condensate sample and the reaction proceeds in thehomogenous phase. As part of the insoluble formulation, the enzyme orenzymes are further optionally bound within a polymer matrix. Anelectrochemical reaction starts on the application of a voltage, thesubsequent current is proportional to the analyte of interest.

Electrical connection of a cartridge device to a housing is made througha plurality of contacts assigned either to the assay detection,temperature monitoring, temperature control, automatic assay starts orelectrochemical detection.

The device has a unique identifier on it which holds informationregarding details of calibration and when the device was made. This datacan be read by the reader device and used to improve the accuracy of theoverall device.

Near the completion of filling a chamber the breath film condensatedissolves patches of salt, the salt is necessary for both fixing thepotential at a silver/silver chloride reference electrode and forproviding a relatively low impedance sample.

This design means there is no manual handling of the sample, the sampleis protected from accidental contamination there are moving parts arerequired to move the sample, and the sample can be guided into a chamberwithout entrapping air. Once condensed the sample is in contact with thecartridge through the transportation and analysis.

Optionally, addition of reagents to a condensate is achieved through apenultimate dissolution of chemicals into the breath condensate duringthe passage of the sample over a surface, or the absorption of thesample into functionalized films.

Exhaled breath is condensed on a functionalised surface, whosefunctionalisation is optimised to maximize the efficiency ofcondensation of a breath film, the surface has been systematicallyoptimised and characterised to minimise droplet formation and insteadform a film across the surface. Unlike previous devices in which amicrofluidic chamber is incorporated the final analysis chamberpreferably has no air vent for the expulsion of trapped air, instead inthe present concept air leaves by the same route as the liquid enters.The liquid is initially guided to the bottom of the chamber, so thechamber is bottom up filled thus air bubbles are not trapped.

The device is laid out so that multiple chemical and biochemical stepscan be carried out on the condensate either in parallel or sequentially.

Distinct patches of reagents are laid out within the device, including:buffers salts and enzymes.

The breath film condensate is guided into the fixed volume sensingchambers. As the solution enters the chamber it sequentially reachesenzymes and the salts. The dissolution of both patches can be distinctor overlapping with respect to time.

The specific analytes of interest for measurement can be detected in thefinal sensing chamber by the use of molecules, macromolecules, ions etc.including but not exclusively: antigens, antibodies, RNA, DNA, proteins,enzymes, ionophores etc. These biochemical reactions are designed togive a signal that is proportional to the analyte of interest.

The inventive device for collecting exhaled breath condensate and fordetermining substances within the condensate includes at least onecondensing zone and at least one sensing zone. The zones are joined insuch a way at to expedite the transfer of condensate to the sensing zonewhilst undergoing any necessary purification or sample enhancement.There is a tapering fluidic lay-out so the film is collected in a largearea which narrows down to a smaller and smaller area henceconcentrating the film onto a final sensing zone.

After a short period of time, and upon adequate sample reaching thesensing zone an assay or measurement can take place upon the sample. Theinitiation of the assay can be automated by a start condition which canbe an electrical signal produced by applying a voltage between twoelectrodes, by reading a voltage generated between two dissimilarelectrodes.

In a further embodiment the temperature of the condensing zone can beset relative to the ambient temperature and the power necessary tomaintain the temperature is both indicative of the rate of exhaledbreath and the power necessary in the change of phase from the gas,vapor and aerosol phase to the liquid condensate phase. Manybiochemical, molecular biology and chemical reactions are temperaturesensitive and so the reaction zone has an integrated heater preferablyon the back side for elevating the temperature above the ambienttemperature and above the condensing zone temperature.

Active heating of the temperature zone allows the assays to be run incold environments such as horse stables where the temperatures can bebelow 10 to 15 Celsius.

The device has been carefully engineered to deliver a device whoseoperation requires minimum interventions from the operator, thereforeremoving one of the biggest sources of inaccuracy due to user error whenperforming manual tasks. In addition, the device has been designed withno moving parts instead a combination of good design and materialsscience is used to cool, guide and prepare the sample, with no complexpumping strategies. The breath condensate film is guided by a fluidiclayout which tapers into a final chamber. The driving force for flow ofthe breath condensate film is provided by a combination of gravity,capillary and tapering channels. In addition, the device can introducemultiple reagents into the sample, all of which are deposited and orpacked and stored upon the device in a dry manner thus optimizing shelflife stability. The entire device is integrated so the sample neverleaves the device from condensation to final detection, thereforeeliminating the risk of sample contamination or sample loss. Similarly,concerns regarding cross-contamination between samples are eliminated asall the wetted parts can be disposed of after each assay. In operationthe device is shielded from the ambient humidity behind walls andvalves, this reduces the co-condensation of ambient humidity which wouldotherwise dilute and contaminate the breath condensate film.

The signal gathered directly from the analyte or measurement of interestcan be calibrated relative to a number of other signals, including:sensing zone temperature, sample conductivity, ambient temperature,breath flow profile, breath condensation profile, breath carbon dioxideprofile.

With many sensing based systems the magnitude of the final signal andthe sensitivity of the signal to the analyte or measurement of interestcan be a variable between sensors from the same manufactured batch andfor sensors from different manufactured batches. In the current systemthe errors caused by sensor variability within batches and betweenbatches are removed both through device characterization at the point ofuse and also by calibration factors determined during the device'smanufacturing. Lastly any changes in the sensitivity of the devices dueto aging can be calibrated for by a calibration factors whose input isthe age of the device.

BRIEF DESCRIPTION OF THE DRAWINGS

The invention is now described with respect to the accompanying drawingswhich show, by way of example only, embodiments of a breath-condensatecollector and analysing device. In the drawings:

FIG. 1 illustrates the layout of a device;

FIG. 1 a further illustrates layout of a device;

FIG. 1 b is a further illustrative layout of a device;

FIG. 2 illustrates a second embodiment of the device, including lids toretain sample and guide flow within the device;

FIG. 3 illustrates further features of a device;

FIG. 4 illustrates the layout of an embodiment of the device;

FIG. 5 illustrates a close-up view of the layout of the sensing zone ofthe device;

FIG. 6 illustrates an example of chemical reactions involved within thesensing chamber

FIG. 7 illustrates an example of an embodiment of a film coating;

FIG. 8 illustrates an alternative layout of the device;

FIG. 9 illustrates an alternative layout of the device;

FIG. 10 is a chart showing raw noise data;

FIG. 11 is a chart showing electrical noise spikes; and

FIGS. 12 a-12 f illustrate a valve system to prevent entry of theambient air into a condensed sample.

DETAILED DESCRIPTION OF THE INVENTION

The analysis of exhaled breath to determine physiological dysfunction ina person or animal has been known for many years. The presence orotherwise of components of the breath can show deficiencies in the body,such as lung function or cell function. To this end, devices have beendeveloped, which aim to collect the exhaled breath, including the morevolatile components, which are otherwise not captured and so escapeanalysis. In many devices, the breath is first condensed to liquid orsolid form, which is then analysed.

There are however problems which need to be overcome in obtaining ananalytical result. Many devices leave the user with the problem ofcarrying out the analysis. Often the condensed sample needs to betransported to a location remote from that where the analysis wascarried out. However, some of the breath components which need to becharacterised, such as hydrogen peroxide, are inherently unstable and sowill have decomposed to an extent before any analysis is carried out.Although steps can be taken to alleviate this problem, such as coolingthe sample in transit and also extrapolating back, based on the timesince the sample was taken, to an estimated value, these steps can bedifficult to carry out and increase the error limits for any particularresult.

Carrying out an analysis in situ, directly the sample is taken,overcomes the above to a large extent, but brings with it the problemsof analysis as, especially where an animal is concerned, this may be ata distance from any building. Also there will be a need for the analystto have calibrated reagents to hand.

The present invention seeks to alleviate the above disadvantages byproviding a hand-held device, which both collects and analyses exhaledbreath.

To achieve this, in a broad aspect, the device firstly collects thecondensate in a collector, then transports a sample of the condensate toan analyser, fluidly connected to the collector where analysis iscarried out using a solid-state analytical element. The use of asolid-state element removes the need for calibration of liquid reagentsand removes the risk of dilution errors. Such a device also provides alonger shelf life than conventional devices and is more easilymanufactured. To reduce the number of moving parts within the device andso increase reliability, the condensate preferably moves through thedevice by capillary action, and also optionally using functionalisedsurfaces to increase flow between regions. Ideally, between condensationof the sample and analysis should be no more than 30 seconds.

In more detail, the exhaled breath is condensed on a surface, optionallyfunctionalised such that any functionalisation is optimised to maximisethe efficiency of condensation and to maximise the flow under gravity orotherwise of condensate phase from the condensing zone to integratedfluidic channel provided. The device is laid out such that multiplechemical and biochemical steps can be carried out on the condensateeither in parallel or sequentially. The channel layout provided, meansthat where chemicals and reagents are utilised during the analysis,these can be sequentially added to a sample as the sample flows over theseries of chemical and reagent zones provided therefor. This arrangementallows unstable reagents, including those which are unstable in thepresence of other reagents, to be prepared or stored in close proximityto one another, yet spatially separated to prevent interaction. Reagentsand sample conditioning additives are able to be added at severaldifferent points within the device.

Finally, the condensate enters one or more sensing chambers, each havinga fixed volume. Any remaining reagents, which can include proteins,enzymes, macromolecules, surfactants, ions etc. necessary for theanalysis can be present here as dry mobile or immobilised formulationsin close or intermediate proximity to the final point of analysis. Thespecific analytes of interest can be detected in the final sensingchamber by the use of such reagents, which can further include antigens,antibodies, RNA, DNA, proteins, enzymes, etc. Analytes to be detectedinclude, but are not limited to: glucose, lactate, ketones, hydrogenperoxide and nitric oxide and may be detected either directly orindirectly.

Detection is preferably carried out electrochemically to increase theaccuracy and reproducibility of results. In one embodiment, two parallelelectrodes are provided, which when not in use are electrically isolatedfrom each other. In the presence of a liquid between the electrodes, asoft short is caused which produces a measurable electric signal, whichcan be used to determine the level of analyte. Such a signal can also beused to determine the arrival of condensate into the cartridge and soinitiate further analytical steps. In a further embodiment, notillustrated, 2 or more electrodes are provided.

The reagents used are designed to give a signal that has a knownrelationship, such as being proportional, to the concentration of theanalyte of interest. The reagents may be present in a form such as drieddown in place, a lyophilized bead or a film or any other suitable form.The advantage of using a dried reagent is that such reagents tend to bemore storage stable and their concentration is likely to be moreaccurately known. The reagent may be a film such as a polymer blendcontaining a biologically compatible polymer, a macro-biologicalmolecule or a mediator. In addition, other reagents such as abiologically-compatible polymer, for example polyurethane, horse-radishperoxidase or a surfactant such as sodium dodecylsulphate can also bepresent. As examples of mediators, then for hydrogen peroxide analysisin particular, potassium ferrocyanide and/or ferricyanide can be used.

As an example, illustrated in FIG. 6 , hydrogen peroxide can be detectedindirectly with the use of horse-radish peroxidase (HRP). The reducedform of HRP initially reacts with the hydrogen peroxide to produce anoxidised form. The oxidised form subsequently reacts with potassiumhexacyanoferrate (II) (potassium ferrocyanide) to produce potassiumhexacyanoferrate (III) (potassium ferricyanide). Potassium ferricyanideis then detected by use of an electrochemical method such as amperometrywhere the current flows from an electrode. The current flowing isproportional to the concentration of the produced potassium ferricyanideand the final current is therefore indirectly linked to the initialhydrogen peroxide concentration in the sample. In detecting theferricyanide species, this is reduced back to the ferrocyanide.

The temperature of the condensing zone can be set relative to ambienttemperature. The power necessary to maintain the temperature differencecan be utilised to determine the rate of generation of exhaled breath.To achieve this, the power necessary to maintain the temperature ismonitored. As this is a function of the thermal energy generated by thechange of phase of the exhaled breath to the liquid condensate phase,measurement of the energy can be converted into a volume of condensateproduced.

In a preferred embodiment, a Peltier device may be used to cool thecondensing zone. The temperature on the face of the cooling zone itselfmay be static or dynamic. In a preferred embodiment the temperaturewould be around 10° C. although it should be appreciated that thetemperature may change depending on the various parameters includingambient conditions. Should atmospheric air be excluded as in certainoptional embodiments of the device then a lower temperature of around 5°C. can be used.

The integrated nature of the device produced allows for the provision ofa device whose operations require minimum interventions from an operatorwhich removes a source of inaccuracy from the results. In addition, thelack of moving parts in preparation and analysis of the sample againimproves the results obtained and also imparts a longer lifetime to thedevice. Further, the device can introduce multiple reagents into asample, all of which reagents are stored within the device in a drymanner, which improves the shelf life of the reagents. Finally, thesample under analysis does not leave the device between the time ofcondensation and final detection, which minimises the risk ofcontamination or loss of sample. Furthermore, as elements used as partof the analysis can be disposed of following use, which again reducesthe risk of cross-contamination. Yet further the analytical elements ofthe device can be incorporated into a removable section, such as acartridge, which allows, once the collection elements of the device havebeen cleaned or otherwise readied for use, a new cartridge to beinserted ready for further use. Separate measurements on differentsubjects can thereby be rapidly made, and analysis on a subject be made,whilst the results are being obtained from a previous subject.Alternatively, measurements of different exhalates made for the samesubject relatively close to each other in time.

It is anticipated that the usable liquid volume within a cartridge isfrom 5-40 μl and preferably 10-30 μl.

On analysis, the signal generated from the analyte or measurement ofinterest can be calibrated relative to a number of other signals,including the sensing zone temperature, sample conductivity, ambienttemperature, etc. Again, therefore the errors caused by sensorvariability within batches and between batches is removed both throughthe device characterisation at the point of use and also by factorsdetermined during the device's manufacturing.

In order to remove variations in analytical results carried out usingelectrodes, due to different concentrations of chloride ion in a sample,then a standard electrode concentration of chloride, typically asaturated solution, can be formed of the sample. This can be achievedthrough the condensate passing over a surface onto or within which achloride, such as sodium chloride, has been added. This can be forexample within a gel layer, from which chloride ions can readily diffuseout. Signals obtained from an electrode can therefore be attributed toan analyte of interest as the electrode response due to the salt can befiltered out.

Signals from the analysis and also from the power usage of the coolingapplied to the condensing zone can be fed to a processor, eitherattached to the device or externally, which then generates the datarequired by the user. Additionally, by performance of a mass-balancecalculation on the condensate collected and the condensate entering thesensing chamber, the device can calculate the distribution of samplethroughout the device and determine whether a cartridge has leaked orblocked, which allows quality checks to be built into the device.

Referring now to FIG. 1 , this illustrates a first embodiment of anintegrated collection and analysis device. The device, generallyreferenced 10, is operatively linked to a mouthpiece (not shown here)through which exhaled breath is directed onto a breath collectionportion 11 having a condensing zone 12. The condensing zone 12 is influid connection with the sensing zone 13 in which analysis of thecollected condensed breath fluid can take place. It will be appreciatedthat when the device 10 is in fact held such that the condensing zone 12is uppermost, then flow of fluid into the sensing zone 13 is facilitatedby gravity. Although not illustrated in FIG. 1 , the condensing zone 12and sensing zone 13 are fluidly connected by one or more channels, toprovide a controlled flow of fluid. The dimensions of a channel are ofan order of magnitude less than those of the overall device 10 althoughthe dimensions of a channel may vary depending on the function of thechannel. Moreover, the dimensions of a channel can vary along the lengthof the channel. In a further non-illustrated embodiment, flow of thefluid from the condensing zone to the sensing zone is controlled bymeans of firstly collecting and holding the condensed fluid in oneregion and subsequently causing a portion of the collected fluid to flowinto the sensing zone in defined aliquots.

In a preferred embodiment the overall dimensions of the device 10 are 66mm×30 mm×5 mm, as illustrated in FIGS. 4 and 5 . The condensing zone 12and the sensing zone 13 are each approximately circular in the preferredembodiment, although they can have a polygonal shape. The size can bevaried to suit the use. The condensing zone 12 preferably is of largerdimension of the order of that of the entire device 10. The sensing zone13 can have a perimeter of approximately between 2-10 mm and ofapproximately 5 mm. The height can be approximately from 75-750 μm andespecially of 100 μm.

FIG. 1 a illustrates features of the device 10 in more detail. Breath iscondensed on the condensing zone 12 and forms a film on the surfacethereof. The condensed fluid exits the condensing zone 12 by capillaryaction, via the channels 18, which lead the fluid to the sensor element19. The sensor element 19 as shown is a combined counter and referenceelectrode, although in a separate embodiment, these can be locatedseparately. The working electrode 20 is housed as part of a ceramicsensor 21. Electrical contact pads 22 at the distal end of the ceramicsensor 21 enable electrical connection with corresponding elements onthe apparatus housing into which the device 10 fits when in use. A cover23 is provided (FIG. 1 b ) which then defines a microfluidic chamberbeneath the cover 23.

In order to aid correct alignment of the device 10 within a housing, keyholes 24 are provided engaging corresponding projections in the housing.Additionally, to aid insertion of the device 10 into the housing thedistal end 25 of the device 10 has a wedge shape. The sensor element 19,ceramic sensor 21 and cover 23 are held in position relative to thedevice body 10 a by an epoxy resin fixing 26, although other fixingmeans, including mechanical, can also be utilised.

In a further preferred embodiment, the or each channel (not illustrated)has a means of allowing air to leave the device 10, for example when thesample flows into a channel. An example of the means may be a furtherchannel or an aperture through which the air can escape. This preventsair from getting trapped within the device 10 as the fluid flows in asthe air has a route by which it may leave. An example of this embodimentis shown in FIG. 4 and in FIG. 5 .

In an alternative embodiment, the device may include an air escapechannel 60 as illustrated in FIG. 4 .

In order to condense the exhaled breath, which comprises a mixture ofgases and vapours, into one volume the condensing zone 12 is providedwith cooling means. The constituent elements of the sensing zone 13 canalso be provided with cooling or heating means, where required, toassist in the analysis of the breath condensate. For example, where anassay incorporates an enzymatically catalysed reaction, it is usuallyadvantageous to carry out the reaction at around normal bodytemperature. An example of a heater which can be used to elevate thetemperature of a reaction is a conductive strip, which can bescreen-printed and secured to the back of a sensor adjacent a sensingzone. On passing a current through the strip, using for example Ohmicheating, the temperature can be controlled using a pulsed voltage acrossthe heater.

Additionally, or alternatively, a thermocouple sensor can also beincluded, preferably printed onto the sensor to achieve intimate contactwith the sensor and give an accurate value for the sensor temperature.An external temperature sensor can however also be used.

To facilitate collection of condensate in one region of the condensingzone 12, the condensing zone 12 can have a coated surface to directcondensed breath optionally towards a particular region of thecondensing zone 12 which particular region can be maintained at a lowertemperature than other regions of the condensing zone 12. The surfacecoating is preferably of a hydrophobic nature, but can also be orhydrophilic where suitable. Additionally, a coating can be providedwhich is both hydrophobic and lipophobic so that both oils and water runreadily off the surface. Such coatings can be those known in the artsuch as perfluorinated polymers, for example that marketed under thetrade name Teflon®. When dried, the thickness of the coating can be inthe range from 1 μm to 15 μm. The coating may swell to a greaterthickness when it comes into contact with the sample. FIG. 7 shows anexample of a coating by a film of a circular area. In this embodiment,the circular area covered by the film coating has a height of 5 μm.

One or both of the condensing zone 12 or sensing zone 13 (see FIG. 2 )can be at least partially covered by a lid 14 or 15 respectively. InFIG. 2 , a lid 14 is shown, located around the perimeter of thecondensing zone 12, which lid 14 acts to retain condensate within thecondensing zone 12. The lid 14, which partially covers the condensingzone 12, also acts to minimise outflow of breath from the collectionportion 11, and restricts loss of breath which does not immediatelycondense on contact with the condensing zone 12. The open area betweenthe perimeter regions allows the exhaled breath to reach the surface ofthe condensing zone 12.

The lid 15, located over the sensing chambers of the sensing zone 13 andthe channels, allows the volume to be controlled, and the sample to beretained, whilst also promoting wicking of the sample into and along achannel or channels. The volume of the sample is kept small through useof the lid to aid analysis, the lid also eliminating turbulent flow andmixing.

FIG. 3 illustrates a device 30, having a further sample preparation zone31, in which initial reagents or other modifiers can be added to thesample to facilitate the analysis in the sensing zone 32. The purity ofthe sample can also be determined prior to the sample passing throughthe sensing zone 32 and into the analysis region 33.

The sensing chambers optionally are operatively connected to a samplesensor which determines whether a sample is present. Additionally, thelevel of sample within a sensing chamber can also be determined. Once apre-set level is reached, the level sensor transmits a signal so thatassay commences automatically without input from the operator. Thisreduces the time at which analysis begins.

FIGS. 8 and 9 show alternative embodiments whereby the sensing zones 42,52 may be laid out within the device 40, 50 either parallel to oneanother below the condensing zone 41, 51 (FIG. 8 ) or sequentially (FIG.9 ).

FIGS. 10 and 11 shows how interference from various sources both knownand unknown, can distort the signal produced. In the preferredembodiment, the spikes within the raw signal will first be identified bythe reader and contribution of the spikes will be removed from the rawsignal before the analyte concentration is calculated.

In an alternative embodiment of a device, not illustrated, the deviceincludes control means to govern the passage of condensed fluid from thecondensing zone to the sensing zone. This allows the condensed breath tobe moved for analysis in a known, controlled manner.

As an example, the breath can be collected with the device so orientedthat the condensation zone and particularly the fluid connection betweenthe condensation zone and the sensing zone is a non-vertical, perhapshorizontal orientation, so that fluid flows relatively slowly or perhapsunevenly therefrom. The cartridge can then be rotated either by hand,but optionally mechanically to provide a vertical orientation. Thisprocess can be made automatic in that a sensor, determining the presenceof a sample, causes a signal to be sent to the cartridge, activating themeans of rotation to the required orientation. The sensor can be linkedvia processor to a spirit level or the like so that current orientationof the cartridge and fluid connection is known.

Additionally or alternatively, vibration means can be included to causemovement of fluid in the condensing zone by vibration of the condensingzone.

In a further alternative embodiment, means are included to preventsaliva from a subject from reaching the condensing zone and socontaminating the breath sample. Saliva is known to have 10-100 timesthe hydrogen peroxide content than is present in the air from the lungs.Such a prevention means must be such as to not interfere with the normalbreathing of the subject, often referred to as a Tidal Breathingtechnique. One option of the prevention means comprises a convolutedpath, and optionally one or more valves. The prevention means can bebrought together on a common housing with the device 10, such thatbreath exiting the prevention means is directed onto the condensing zone12. The prevention means, usually formed into a mouthpiece into which apatient breathes, is preferably replaceable once used, to improve thehygiene and accuracy of the apparatus.

In a yet further embodiment means can also be included to preventhumidity from the ambient air from condensing in the condensing zone andcontaminating the sample, primarily by dilution, also possibly byintroducing air-borne contaminants. This is illustrated in FIG. 12 .

One of the potential sources of contamination of the exhaled breathcondensate is the co-incidental condensing of humidity from the ambientair, which will be an uncontrolled process causing uncontrolled hydrogenperoxide concentrations. The valve system illustrated in FIGS. 12 a-12 fprevents the ambient air from readily making its way to the Peltiercooler and being condensed within the cartridge. Additionally, the mouthpiece 120 allows the effective use of accessories to be used ifrequired, such as: saliva traps, filters, flow restrictors and noseclips. Therefore, the device can be used in several modes of operationdepending on whether or which accessories are used.

The use of valves and baffles ensures that the majority of the exhaledbreath is now forced to pass within the vicinity of the cooledcondensing zone of the cartridge, ensuring a good efficiency incondensing the exhaled breath vapour. The valved mouth piece can haveone or more chambers within it, with chambers directly connected orconnected via a valve. In the disclosed embodiment there are threechambers, with a valve between Chamber One 121 and Chamber Two 122,whilst Chamber Two 122 and Chamber Three 123 are in direct contact. Inthe illustrated embodiment, the mouth-piece is securable to a housing bymeans of external lugs 128.

The logic of the valves is that all the valves are normally closed whenthe device is not in operation. Upon inhalation Valve Three 126 opens,whilst Valve One 124 and Valve Two 125 remain closed. Upon exhalationValve Three 126 closes and Valves Two 125 and One 124 open. The deviceprovides for the immediate analysis of exhaled breath condensateanalytes, where the ambient air is precluded from the cartridge behindone or more normally closed valves. The device directing air into thelungs and from the lungs to the cartridge can have one or more chamberslaid out either in series or parallel.

As an example of valves suitable for the present invention, diaphragmvalves can be cited. Diaphragm valves are used such that when a user isinhaling one valve opens to allow air in, whilst the other is closed.Upon exhalation, the valve state is reversed.

The device is designed to ensure the efficient condensation of vapourfrom the breath by directing the exhaled breath across the surface ofthe cartridge's condensing zone. Typically, a condensate sample will beformed over a number of breath cycles taken over, for example, 60seconds to collect sufficient breath condensate. Chambers can beconnected to one another directly or connected via valves. During thebreath cycle the flow of air is controlled to allow air into the lungs,whilst not exposing the cartridge to the ambient air; subsequently uponexhalation the exhaled breath is led along a path where the breath ispassed over the cold zone before venting to the ambient. The judicioususe of valves means ambient air is precluded from directly reaching thecartridge when the device is either operational or non-operational, withthe logic of the valves as shown in Table 1. Additionally, the devicehas one or more ports which allow for air/gas exchange between the user,the ambient air and the air within the device. These ports can be usedin conjunction with accessories including saliva traps, flowconstrictors and filters etc., allowing several modes of action. Lastlythe device can be used in conjunction with a device to prevent the flowof air through the user's nasal passages so as to force a mode ofbreathing where air passes only through the mouth.

TABLE 1 Operation Valve Logic Comments Inhalation Valve Three: open Thisis to allow the user to inhale Valve Two: closed through the devicewhilst preventing the Valve One: closed air that is being inhaledflowing over the condensing zone. Exhalation Valve Three: closed Thevalve logic means the exhaled Valve Two: open breath has to follow apath where it Valve One: open flows within the vicinity of the cooledcondensation zone on the cartridge leading to a more efficientcondensation of the vapour within the exhaled breath. Not in Use ValveThree: closed When not in use, all the valves are Valve Two: closedclosed and therefore reduces the Valve One: closed amount of ambientvapour that can be accidentally condensed within the device.

In a still yet further embodiment of the device, the flow rate of theexhaled breath can be monitored, allowing a user or a supervisingindividual to allow the control of the flow rate or issue guidance. Thesensor means for the flow rate may therefore be included within thedevice. The sensor thereby transmits real time data, which can providevisual or audio feedback, so that the breathing rate can be adjusted tostay within acceptable boundaries. Additionally, the breathing rate canbe utilised as part of the diagnostic determination.

An exemplary device may have the following three modes of operation:

Mode One—Analyse a subject's status from one or more real-time signalsincluding: breath exhalate carbon dioxide levels, breath flow rate,breath water content, breath pressure; one or more of these signals areused to determine the status of the user, and/or their lungfunctionality.

Mode Two—Analyse a subject's status from a collected exhaled breathcondensate, this measurement can be corrected for parameters such asbreath exhalation profile, breath water content, breath carbon dioxidelevels etc. For example, the carbon dioxide signal can be used tocalculate the fractionated analyte concentration from the measuredanalyte concentration.

Mode Three—Analyse a subject's status by combining the two modesdescribed above, so that a breath condensate can be reported within thecontext of the overall exhaled breath profile and breath gas analysis.

In a further exemplary embodiment, a mouthpiece employs an arrangementof baffles to minimise the chance of aerosol from the mouth reaching thecondensation zone. In one arrangement air entering the mouthpieceencounters a first baffle which charges the air velocity by around 90°.A second baffle then causes an approximately 180° change of direction.In this manner large droplets from the mouth are caused to drop out ofthe airflow, allowing vapour from the lungs through.

The cartridge device is typically held, replaceably, within a housing toform an analysis apparatus, which housing includes features such ascooling, heating, processing means which can be used in co-operationwith the cartridge device. The housing may comprise a cooling means,such as a Peltier plate, for cooling the cartridge to a suitabletemperature for condensation. The cooling means may alternatively bepart of the cartridge.

The housing may comprise a heating means to heat a reaction zone whichitself forms part of the cartridge. The heating means may be arranged inthe housing or as part of the cartridge. There may be an electricalconnection between the housing and the cartridge. The heating means maybe an Ohmic heater.

Heating and cooling means enable both condensation to a breathcondensate film and subsequently performance of enzymatic assays uponthe film. Furthermore, the sensor may be heated. Active heating of thesensor allows for operation of the cartridge in environments cooler than10 to 15 Celsius.

The housing may comprise a series of baffles to remove saliva aerosolfrom a vapour sample, so that substantially only vapour reaches thecartridge. Alternatively or additionally, a series of baffles may beprovided in the cartridge. Yet alternatively, a single baffle may beprovided in each of the housing and the cartridge.

The housing may comprise a valve system to provide at least two flowpaths through the complex device. Thus, an exhalation breath may bedirected through a first flow path and an inhalation breath may bedirected through a second flow path.

The housing may further comprise a flow rate sensor for measuring breathflow rate.

The housing may further comprise a carbon dioxide sensor for measuring acarbon dioxide concentration in breath.

The housing may further comprise a humidity sensor. There may be morethan one humidity sensor, for sensing the humidity of breath or ambientair, for example.

The housing and/or the cartridge, preferably the cartridge may furthercomprise a temperature sensor for measuring breath temperature.

The housing may further comprise a pressure sensor for measuring breathpressure during exhalation or inhalation.

The housing may further comprise an electronic interface for providinginformation from one or more sensors to an external device and/or forreceiving electrical energy from an external source. The electronicinterface may provide information in an analogue or digital form.

The housing may further comprise a data processing unit. The dataprocessing unit may comprise an analogue to digital converter. Thehousing may further comprise a transmittal means to transmit informationor data to an external device. Additionally, a data storage means can beincluded. The housing may comprise an electronic interface for aremovable data storage means.

The housing may further comprise an audio output to provide a user withfeedback and/or instructions to assist the user with keeping breathparameters (such as pressure or flow rate or the like) within a desiredrange.

The housing may further comprise a display. The display may provide auser with information about a breathing cycle in real time or in nearreal time. The display may provide a user with feedback and/orinstructions to assist the user with keeping breath parameters (such aspressure or flow rate or the like) within a desired range.

The apparatus can combine any number of signals to determine a patient'sstatus or to calibrate a signal. Additionally, the device can open andclose valves in response to defined conditions being met, for examplethe collection of fractionated breath by triggering valve when carbondioxide level criteria are met.

The apparatus is light and portable so can be picked up and placed infront of the mouth, and can be operated without being physicallytethered to a power supply or third-party device.

The apparatus is designed to be used with tidal breathing for greaterpatient acceptance, relative to previous devices which would requireforced air manoeuvres.

The apparatus aims to perform all the necessary functions involvedwithin the workflow of collecting and analysing the breath condensatewithout manual interference or intervention by a user or clinician. Thedevice may have both real-time sensing and analysis of the breath andphysical parameter associated with breathing.

In one preferred embodiment the breath condensate film is directedimmediately from the subject's mouth through a tortuous flow path to thefully integrated apparatus (i.e. housing plus cartridge), where thebreath is condensed into a breath film condensate upon a cooled zone.The resulting condensate film is immediately guided by a combination ofcapillary forces and gravity across a functionalised surface to achamber. The film enters the chamber by following down the chamber'ssides and filling the chamber from the bottom up. Finally, thecondensate dissolves several salt patches; the dissolution of salt intothe breath film condensate is electrically/electrochemically monitoredand checked for the correct dissolution profile as part of onboard assayquality control. An incorrect profile is used to reject the cartridge.

One inventive concept relates to a single integrated device forcondensing breath as a film and analysing analytes within the exhaledbreath condensate film. The device performs all the necessary functionsinvolved within the workflow of collecting and analysing the breathcondensate without manual interference or intervention by a user such asa clinician. The device includes a least one temperature zone for breathcondensation that is integrated with at least one sensing zone formeasurement upon the condensate.

In the preferred embodiment of the apparatus the condensation zone isconnected to the patient's mouth by a short tortuous flow path, designedto allow the passage of vapour from the lungs, and in particular, thealveolar part of the lung, whilst excluding aerosol from the mouth etc.Following condensation of exhaled breath, the film flows under theinfluence of gravity and capillary forces into a chamber, which isclosed on five sides; the film flows down the sides of the chambereffectively filling the chamber from the bottom up.

Near the completion of filling the chamber the breath film condensatedissolves patches of salt, the salt is necessary for both fixing thepotential at a silver/silver chloride reference electrode and forproviding a relatively low impedance sample.

The invention claimed is:
 1. A cartridge device for collecting andanalysing a breath condensate, the device comprising a condensation zoneto condense exhaled breath from a subject into a condensate, thecondensation zone, being operably connectable to a cooling means, thedevice including one or more further discrete regions for detection ofone or more analytes in the condensate and measurement of the one ormore analytes, the cartridge device further comprising a fluid pathconnecting the condensation zone to the or each discrete region, andwherein a surface of the or each discrete region includes a respectivesurface coating, said respective surface coating including one or morereagents to engage the condensate in the respective discrete region anddetermine composition, and wherein the cartridge device is configuredsuch that the condensate will form a film in the condensation zone, andwherein the condensation zone includes a condensing surface onto whichthe exhaled breath condenses to form the condensate as the film, and thecondensing surface is arranged to form a contact angle of 20° with thebreath condensate from the subject.
 2. The cartridge device according toclaim 1, wherein the device includes analysis initiation means to detectthe presence of the condensate.
 3. The cartridge device according toclaim 1, wherein the or each discrete region has a specified volume,which allows the measurements to be calculated based upon the respectivevolume.
 4. The cartridge device according to claim 3, wherein thespecified volume of the or each discrete region is up to 4 μI.
 5. Thecartridge device according to claim 1, wherein the or each discreteregion has a specified volume such that there is an analyte detectionzone of the or each discrete region whose volume is less than apredetermined volume of the condensate.
 6. The cartridge deviceaccording to claim 1, wherein the respective surface coating has athickness in a range of 1 μm to 15 μm.
 7. The cartridge device accordingto claim 1, wherein the or each discrete region includes at least a pairof electrodes in operable connection with the condensation zone.
 8. Thecartridge device according to claim 7, wherein the cartridge device isconfigured to vary a difference in potential between the pair ofelectrodes.
 9. The cartridge device according to claim 1, wherein thecartridge device is configured to have a further reagent added to saidcondensate in a further discrete preparation region.
 10. The cartridgedevice according to claim 1, wherein the cartridge device is configuredto have a further reagent for analysis of the condensate loaded into thecondensate during passage of the condensate from the condensation zoneto a respective one of the discrete regions.
 11. The cartridge deviceaccording to claim 1, wherein at least one of the one or more discreteregions has a perimeter ranging from 2-10 mm.
 12. The cartridge deviceaccording to claim 11, wherein the at least one of the one or morediscrete regions has a perimeter of 5 mm.
 13. The cartridge deviceaccording to claim 1, wherein at least one of the one or more discreteregions has a height of from 75-750 μm.
 14. The cartridge according toclaim 13, wherein the at least of the one or more discrete regions has aheight of 100 μm.
 15. The cartridge device according to claim 1, whereinat least one of the one or more discrete regions comprises a chamber,the chamber being enclosed on five sides with a sixth side open for thecondensate to enter said chamber and for displaced air to escapetherefrom.
 16. The cartridge device according to claim 1, wherein thecartridge device is configured to measure interference to a measurementof the analyte.
 17. The cartridge device according to claim 1, whereinthe cartridge device is configured to determine power supplied to thecondensation zone.
 18. The cartridge device according to claim 1,wherein the device further comprises a hole or channel through which aircan escape from the device, said hole or channel connecting at least oneof the one or more discrete regions with atmosphere.